Extreme Light Infrastructure (ELI) and Hadron Therapy D. C ... Light Infrastructure... · M. Petrus, A. M. Bratu, S. Banita Department of Lasers, National Institute for Laser, Plasma

Extreme Light Infrastructure (ELI) and Hadron Therapy

D. C. Dumitras, R. Dabu, D. C. A. Dutu, C. Matei, A. Achim, M. Patachia,

M. Petrus, A. M. Bratu, S. Banita Department of Lasers, National Institute for Laser, Plasma

and Radiation Physics, P. O. Box MG-36, 409 Atomistilor St., 077125 Bucharest,

Romania E-mail: [email protected]

Abstract Hadron therapy is a part of radiation therapy, which

uses not only beams of high energy ions, but also π–mesons, neutrons, electron beams, X- and gamma rays to irradiate cancer tumors.

Proton therapy is an effective treatment especially against cancers located in areas which are inaccessible to surgeon’s instruments or which are hard to treat by radiotherapy.

Among the advantages of proton therapy we mention: the proton beam scattering on the atomic electrons is weak and thus there is less irradiation of healthy tissues

in the vicinity of the tumor; the deceleration length for a proton with given energy is fixed, which avoids undesirable irradiation of healthy tissues behind the tumor; the well localized maximum of the proton energy losses in matter (the Bragg peak) leads to a substantial increase of the radiation dose in the vicinity of the proton stopping point.

Our work will first describe the benefits of proton therapy vs. X-ray and the present status of the art of medical applications of proton beams generated by conventional accelerators of charged particles (synchrotrons, cyclotrons, linacs).

A laser-based accelerator is fairly attractive because of its compactness and of the additional possibility it offers of controlling the proton beam parameters.

For medical applications, the maximum proton energy must be in the range of 230 to 250 MeV.

The present-day laser parameters (pulse energy, pulse duration, peak intensity and focal spot size) are not yet optimized for the intended applications.

Laser proton accelerators are based on the fact that the nonlinear interaction of high-power laser radiation with matter is accompanied by the efficient conversion of laser energy into the energy of fast particles.

In the last years, energetic proton beams with high beam quality have been produced from thin metallic foils irradiated by ultraintense short laser pulses (I > 1018

W cm-2). These proton beams have a number of unique properties, including high brightness and

ultralow emittance, they are extremely laminar, collimated, with a smooth angular distribution and a duration of the order of tens of femtosecond till one picosecond.

The characteristics of targets used in laser proton accelerators are very important and the solutions to increase proton generation efficiency will be discussed.

Other applications of proton beams, such as fusion, radiotherapy, PET and spallation will be shortly presented.

The last section of the work will be dedicated to the Extreme Light Infrastructure (ELI), which will be the first pan-European large-scale facility dedicated to multidisciplinary applications.

It will be an Exawatt-class laser, approximately 1000 times more powerful than either existing laser.

This gigantic scientific machine would serve to investigate a new generation of compact accelerators delivering energetic particles and radiation beams of femtosecond (10-15

s) to attosecond (10-18

s) duration and intensities exceeding IL > 1025 W/cm².

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In this way, it will be possible to explore for the first time the intensity territory of ultra-relativistic regime (IL > 1023

W/cm²), where a plethora of novel effects will be studied: X-ray generation, γ-ray generation, relativistic self focusing, high-harmonic generation, electron and proton acceleration, neutron and positron production, as well as manifestation of nonlinear QED effects.

Finally, the present situation and the future plans to increase the laser power capability at INFLPR, Bucharest, will be discussed.

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Dan C. Dan C. DumitraDumitraşş, R, Răzvanăzvan DabuDabu, Doru C. A. , Doru C. A. DuDuţţuu,,ConsuelaConsuela Matei, Cristina Matei, Cristina AchimAchim, Mihai , Mihai PaPaţţachiaachia,,Mioara Mioara PetruPetruşş, Ana Maria , Ana Maria BratuBratu, , ŞŞtefan tefan BăniBăniţţăă

Department of Lasers,

National Institute for Laser, Plasma and Radiation Physics,

P.O. Box MG-36, 077 125 Bucharest-Măgurele, Romania

E-mail: [email protected]

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DEFINITION:Hadron – is a bound state of quarks

RADIOTHERAPY WITH NEUTRONS, RADIOTHERAPY WITH NEUTRONS, PROTONS AND CARBON IONS BEAMSPROTONS AND CARBON IONS BEAMS

PREDEAL, ROMANIAPREDEAL, ROMANIAFEBRUARY 27 FEBRUARY 27 –– MARCH 1, 2009MARCH 1, 2009

1.2.3.4.5.6.7.

OverviewOverview

Hadrons are held together by the strong force, similarly to how atoms are held together by the electromagnetic forceThere are two subsets of hadrons: baryons and mesonsThe most well known baryons are protons and neutrons

Proton – is a subatomic particle with an electric charge of +1 elementary chargeIt is found in the nucleus of each atom but also stable by itselfHas a second identity as the hydrogen ion, H+

It is composed of 3 even more fundamental particles comprising two up quarks and one down quark

IntroductionIntroduction

IntroductionProton therapy vs. X-raysPresent status of the artLaser-based particle acceleratorsOther applicationsExtreme Light Infrastructure (ELI) projectConclusions

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Hadron therapy is a part of radiation therapy, which uses not only beams of high energy ions, but also π-mesons, neutrons, electron beams, X- and gamma rays to irradiate cancer tumors

Proton therapy is an effective treatment especially against cancers located inareas which are inaccessible to surgeon’s instruments or which are hard to treat by radiotherapy (brain tumors, in areas close to the spinal cord, inside the eye, etc.)

Advantages of proton therapy: - the proton beam scattering on the atomic electrons is weak and thus there is less irradiation of healthy tissues in the vicinity of the tumor - the deceleration length for a proton with given energy is fixed, which avoids undesirable irradiation of healthy tissues behind the tumor - the well localized maximum of the proton energy losses in matter (the Bragg peak) leads to a substantial increase of the radiation dose in the vicinity of the proton stopping point

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IntroductionIntroduction Proton therapy vs. XProton therapy vs. X--raysrays

Proton therapy vs. XProton therapy vs. X--raysrays Proton therapy vs. XProton therapy vs. X--raysrays

Main difference between X-rays and particles is their different biological action and different depth dose distributionX-rays: the dose decreases exponentially for larger penetration depths →deep-seated tumors have to be irradiated for many parts in order to distribute the non-wanted dose in front of the tumor over a large volume when delivering a lethal dose to the tumor (up to 10 fields in Intensity Modulated Radio Therapy – IMRT)

- main problem: induction of secondary tumorsParticle therapy: hadron beams have an inverse dose profile that produces a greater dose to the tumor than to the healthy tissue in the entrance

−by Intensity Modulated Particle Therapy (IMPT), hadron beam is guided according to the shape of the zone to be treated (the tumor can be delineated in all its contours with a precision of 2 – 3 mm)

−changing the ion energy shifts in depth the position of energy deposition, allowing proton therapy of deep-seated tumors

Ions are better for radio-resistant tumors while protons minimize the risk of appearance of secondary tumors

One of the main challenges in radiation therapy is to deliver a substantially high and homogeneous dose to a tumor, while sparing neighboring healthy tissues

Proton beams with high quality, i.e., with sufficiently small energy spread, ∆E /E, is of fundamental importance

Relative dose deposition of different particles in human tissue

If the proton beam is not completely monoenergetic, the energy depositionis modified and the dose is deposited on a longer path

For a precision of ~ 1 mm, the energy spread needs to be ∆E < 0.3 MeV

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Left: image of the human brain superimposed with a deposited doseby an X-rays irradiation; right: same, but using protons

⇒ in proton therapy, the dose is deposited much more locally

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The importance of dose sparing to healthy tissue in preventing side effects is shown in the Proton (above) vs. X – ray (below) dose distribution

for spinal treatment (pediatric meduloblastoma)

1111Compared relative biological effectiveness (RBE) for proton, carbon and neon beams versus linear energy transfer (LET)

One of the major advantages of heavy ion tumor therapy is the increase in relative biological effectiveness (RBE) of particle beams; it depends in a complex way on different factors like e.g. ion type and energy, depth in tissue, dose level and the tissue type

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Proton therapy vs. XProton therapy vs. X--raysrays Proton therapy vs. XProton therapy vs. X--raysrays

Proton therapy vs. XProton therapy vs. X--raysrays Present status of artPresent status of artBy now, proton beams with the required parameters have been obtained using conventional accelerators of charged particles (synchrotrons, cyclotrons, linacs)Both linear particle accelerators (linacs) and circular accelerators use a very lowenergetic thermal particle source (a few 100 keV) and then an accelerating sectionIn the linac, the acceleration is done by putting succesively linear acceleratingsections in a straight line; an electromagnetic field that is generated within a cavity accelerats the particles and electromagnetic magnets (quadrupoles) focus them to make sure that the particles do not divergeIn circular accelerators, particles move in a circle and are bent by electromagnets; the ring structure has the advantage that particles can transit indefinitely

Linac accelerator used for PET

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The basic process of the proton therapy application. A monoenergetic proton beam is first spread in energy and in space.

Protons cross a plastic mask that helps to compensate the energy loss necessaryto deposit the proton energy peak (Bragg peak) in the concerned region

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Present status of artPresent status of art Present status of artPresent status of art


GANTRY – a device that provides multi-directional irradiation of a lying patientDue to the size of the accelerator and mainly of the transport lines, an entire building (the size of a football field) is needed to house this equipment, which can weigh up to 900 tons

Plan of Rineker Proton Therapy Center (RPTC - München), using one accelerator and 5 rooms for treatment. The total size is 100 x 45 m

Proton beam handling and focusing is expensive and difficult

Eccentric or isocentric machines are used to transport proton beams from the last section of the accelerator to the tumors

These structures are made up of heavy magnet for beam deflexion weighing from 100 to 200 t and having a diameter from 4 to 10 m

An average cost for a specialized centre is 150 M€

LOMA LINDA (Los Angeles, USA)– first hospital-based proton therapy facility in the world– patient treatments were started in 1990– up to now more than 5000 patients have been treated– recently reached the capability to treat 1000 patients per year

The synchrotron: maximal proton energy – 250 MeV; irradiation period – 2.2 s; diameter size – 12 m

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For a full proton treatment: - usually 60-71 Gy are needed that are deposited in doses of 2 Gy

per session for 5 days a week - the dose is given within ~ 1 minute- the estimated cost (all inclusive) per treatment session is ~ 1000 €

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NPTC (The Northeast Proton Therapy Center – Boston, USA) has been treating patients with proton beams since November 2001. Over 200 patients were treated in the first year of operation

- four operating beam lines- rotating Gantries- patient – positioning system- deeper proton penetration

Allow a wider range of clinical applications:

- head and neck sites (ocular melanomas – 96% success; chordoma – 98% success; paranasal sinus – 80% success)- prostate- hepatocellular carcinoma- lung cancer- rectal carcinoma- pediatric tumors

The proton cyclotron (230 MeV) produced by industry (Ion Beam Applications – IBA)

(size: 4 m diameter; weight: 220 tons)


Present status of artPresent status of artPARTICLE THERAPY CENTERS:PARTICLE THERAPY CENTERS:


NORTH AMERICA, CANADA:

Francis H. Burr Proton Therapy Center (NPTC), BostonLoma Linda University Proton Therapy Center, CAUniversity of California, Crocker Nuclear Lab, CAMidwest Proton Radiotherapy Institute, BloomingtonM.D. Anderson Proton Therapy Center, Houston, TXUniversity of Florida Proton Therapy Institute, JacksonvilleNational Association for Proton TherapyHampton University Proton Therapy Institute, Hampton, VIANorthern Illinois Proton Treatment and Research CenterThe Roberts Proton Therapy Center, PennsylvaniaTRIUMF Proton Therapy Facility, Vancouver

EUROPE:

Proton Therapy Centre, Paul Scherrer Institute (PSI), SwitzerlandCentre de Protonthérapie, Orsay, FranceCentre Antoine Lacassagne, Nice, FranceCentre of Oncology, Clatterbridge, UKProton Therapy, Charité/HZB (formerly HMI), Berlin, GermanyBiophysics and Therapy Centre, GSI, Darmstadt, GermanyRadiation and Radiobiological Research, JINR, Dubna, RussiaMedical Physics Department, ITEP, Moscow, RussiaGatchina Medicine Radiation Facility, St. Petersburg, RussiaCATANA, INFN, Catania, Sicily, ItalyRPTC, Munich, GermanyWPE, Essen, GermanyParticle Therapy Center, Malburg, GermanyIon Beam Therapy Center, HIT, Heidelberg, GermanyNRoCK, Kiel, GermanyTERA Foundation, Novara, ItalyThe Svedberg Laboratory, Uppsala, SwedenMedAustron, Wienerneustadt, Austria

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2222Example of a screen used during treatment

showing beam parameters monitored in real time

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The Large Hadron Collider (LHC)

LHC is a gigantic scientificmachine for accelerating protons

It operates at CERN Geneva

It is located inside a circular underground tunnel of 27 km circumference (8.6 km diameter)

It will accelerate protons up toan energy of 14 TeV

The cost for the LHC machinealone is about 3 G€

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Present status of artPresent status of art

Present status of artPresent status of art LaserLaser--based particle acceleratorsbased particle accelerators

ASIA:

HIMAC, Chiba, JapanHyogo Ion Beam Medical Centre, JapanPMRC, Tsukuba, JapanWERC, Wakasa Bay, JapanGHMC, Gunma University Heavy Ion Medical Center, JapanWanjie Proton Therapy Center, Zibo, China

AFRICA

iThemba Research Labs, Radiation Group, South Africa

A laser-based accelerator is fairly attractive because of its compactness and of the additional possibility it offers of controlling the proton beam parameters

There are two possible ways of using a laser beam accelerator:- simply replacing the conventional proton accelerator- delivering the laser radiation to the target where its energy is converted into the energy of fast ions (simplifies the technical problems related to the generation and transport of the ion beam and reduces costs substantially)

For medical applications, the proton beam intensity must be in the range 1010 to 5x1010 protons per second and maximum proton energy must be in the range 230 to 250 MeV

Two conditions are the most demanding for the laser accelerator:- a highly monoenergetic proton beam with ∆E/E = 10-2

- the system duty factor (the fraction of the time during which the proton beam can be used) must not be smaller than 0.3

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a) Conventional Gantry system: (1) deflecting magnets; (2) quadrupolelenses; (3) positioner; (4) dose delivery system and dose monitoring; (5) treatment room; (6) concrete protection

b) Laser-based proton accelerator (by using a set of mirrors, the laser beam could be relayed much closer to the patient, greatly reducing the need for large and costly beam transport lines and gantries)

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LaserLaser--based particle acceleratorsbased particle accelerators LaserLaser--based particle acceleratorsbased particle accelerators

Targets used for proton acceleration are a few centimeters in size

The target can be placed as close as possible to the patient, which means that only small mirrors are required for laser beam transport instead of heavy and costly magnets

Although particle selection and focusing systems will be necessary after the target, the whole equipment should be much lighter, smaller and affordable than current machines

The principle of laser-based proton accelerator: the focused laser beam hits the target and protons are ejected from the rear surface


Laser proton accelerators are based on the fact that the nonlinear interaction of high-power laser radiation with matter is accompanied by the efficient conversion of laser energy into the energy of fast particles

Energetic proton beams with high beam quality have been produced in the last ten years from thin metallic foils (usually aluminum) irradiated by ultraintense short laser pulses (I > 1018 W·cm-2)

Protons accelerated from solids originate primarily from hydrogenated contaminant layers of water vapor and hydrocarbons on the target surface

These proton beams have a number of unique properties, including high brightness (~1012 ions in subpicosecond-scale bunches) and ultralow emittance, they are extremely laminar, collimated (~15o half-angle with a divergence decreasing with the beam energy), with a smooth angular distribution and a duration at the source of the order of tens of femtosecond till one picosecond

For the human body it is not relevant if protons arrive continuously or pulsed, since human cells do not react differently when a source is continuous or pulsed with a repetition rate higher than 10 Hz

MECHANISM– when multiterawatt laser radiation interacts with a target, matter is ionized in

an interval shorter than a single optic oscillation period of the laser radiation, producing a collisionless plasma

– under the action of the laser radiation the electrons are expelled from a region on the foil with transverse size of the focal spot

The basic mechanism involved in the production of these proton beams is electrostatic acceleration of protons at the target rear (non-irradiated) surface. The proton acceleration is achieved by charge-separation electric fields (gradients of the order of MV µm-1) induced by the laser-accelerated hot electrons produced at the front surface going through the target and emerging from the rear

Till now, protons with energies up to 60 MeV and heavier ions with energies up to ~ 7 MeV per nucleon have been measured; efficiencies between 0.2% and 6.0% were observed

Electron energies were measured in the range of hundreds of MeV

The present-day laser parameters (pulse energy, pulse duration, peak intensity and focal spot size) are not yet optimized for the intended applications

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Laser intensity required to achieve 200 MeV as maximum proton energy for various laser pulse durations and target thicknesses (based on fluid model, Fuchs et al. 2005)

The proton energy has to be high enough to penetrate through several centimeters of tissue, that is, 60 MeV corresponding to eye tumors or to tumors in small animals for preclinical studies, and 250 MeV corresponding to the deepest zones to be treated (25 cm)

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LaserLaser--based particle acceleratorsbased particle acceleratorsIn the case of maximum proton energy versus intensity, a generaltendency can be estimated for two different intensity regimes

For laser intensities Iλ2 < 1019 W·cm-2 µm2 the tendency is mostly Ep ∝ I, while for Iλ2 > 1019 W·cm-2 µm2 the tendency is closer to Ep ∝ I0,5

(fluid based model, Mora 2003, Antici 2007)

LaserLaser--based particle acceleratorsbased particle accelerators

Robson et al. (2007) predicts that 200 MeV protons required for oncology should be achievable with 1 ps laser pulses focused to 4x1021 W·cm-2 (with a 25 µm Al target)The increase of the maximum proton energy is much slower than previously thought (based on two-phases model with 3D effects)Even higher intensities are required to produce the number of 200 MeV protons required for oncology

Experimental data reported bydifferent laboratories. Lines havebeen calculated by Antici (2007) with rear surface acceleration(RSA) model assuming 20 µm thick targets and a 10 µm FWHM laser spot size


A power scaling of the form Epmax = a·Ib with b= 0,5 ± 0,1 provides a good fit to the complete data set (individual fits for 10 µm and 25 µmtargets are obtained with b = 0,5 and 0,6, respectively) (Fuchs et al. 2005, Robson et al. 2007)

This indicates that the maximum proton energy is proportional to the fast – electron temperature, which scales as the ponderomotive potential

(∝ (Iλ2)1/2 ); the result is in very good agreement with proton energy measurements at intensities between 1018 W·cm-2 and 1020 W·cm-2 (Clark et al. 2000, Allen et al. 2003)

A decrease in target thickness results in an increase in the maximum proton energy and in the energy conversion efficiency (Antici 2007)

However, if the target is too thin ( ≤ 8 µm), protons are not accelerated to high energies (the rear surface is massively perturbed by the laser amplified spontaneous emission – ASE)

ASE-induced effects have previously been shown to affect the spatial distribution and reduce the maximum energy of ions accelerated from thin targets

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A solution to increase proton generation efficiency is to use multi-layer targets, where a thin foil is used as a target and its rear surface is coated with a thin hydrogen layer (Bulanovet al. 2002)

Scheme of a two-layer targeta) Density distribution of heavy ions, protons, andelectrons and dependence of the electric field onthe x coordinateb) The form of two-layer target in the r, x planec) Shape of a curved two-layer target in the r, xplane

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Alternative paths for proton energy increase:

- by a controllable large preplasma in front of the solid (increases the number and the temperature of the accelerated electrons)

⇒ it can be achieved by using a controlled gas (e.g. He) in front of the target (“gas bag targets “)

- by the relativistically transparency regime; the laser pulse interacts with the whole volume of an ultra thin (30 – 500 nm) dense target and accelerates efficiently the whole electron population

⇒ it requires ultra-high temporal contrast pulses

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Potential applications of a laser-based source of ions:

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Other applicationsOther applications

1.


proton oncology

fast ignitor beam for laser-driven fusion

proton imaging (radiography)

medical isotope production (e.g., for positron emission tomography – PET)

studies related to nuclear spallation physics

injection into large-ion accelerators

astrophysics

fundamental physics

FUSION – the use of protons for the fast ignition:

protons are used as energy transfer medium to heat the ignition regionprotons have the advantage, compared to fast electrons, that they have a much better energy deposition and can be focused to the hotspot due to their Bragg peak, they are able to deposit their energy very locally and are therefore very suitable for fast ignitionmoreover, protons can be focused to a small spot generating a more intense proton beam on the hotspot

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2.

Other applicationsOther applications3.


4.

Other applicationsOther applications Extreme Light Infrastructure (ELI) Extreme Light Infrastructure (ELI) projectproject

RADIOGRAPHYan interesting application of laser-generated proton beams relies on their unique spatial properties of high laminarity or low emittancethey can be used in radiography, producing images with high spatial resolution; since protons are sensitive to electric fields, they are therefore able to probe electric fields as they can penetrate deep into matter, depositing their energy very locally (Bragg-peak), they can radiograph dense objectsusing the time of flight (TOF) technique they allow detecting details of a few microns on picoseconds timescale

PET (Positron Emission Tomography)– a nuclear medicine technique used for medical imaging– uses positron emitters to characterize the biochemical function of cells, organs, and body structures in vivo, producing a three-dimensional image or map of functional processes

To produce intense radioisotope sources for PET (> 109 Bq of 11C or 18F are commonly used per patient dose), a large number of protons with energy ~ 10 MeV is required

Recently, it was measured up to 107 Bq of 11C and 105 Bq of 18F produced by laser-accelerated protons

Operating mode of PET

SPALLATIONis the process in nuclear physics when a very high-energy proton bombards a heavy atomic nucleus and neutrons are emitted in the nuclear reaction

at high proton energies (~ 1 GeV), for every proton striking a heavy nucleus, 20 to 30 neutrons are expelled

there are two spallation processes using protons: the direct and the indirect spallation

- the direct spallation is when the proton directly hits the heavy atomic target (e.g. 90Sr, 137Cs), generating neutrons and more stable heavy ion isotopes

- the indirect spallation is when protons bombard a heavy atomic element and neutrons are generated that activate the transmutation process (this process is much more efficient than direct spallation, since the energy needed for transmutation is about 1/3 the energy needed for creating the isotopes)

spallation processes are one of the main possibilities for transmutation of radioactive isotopes; transmutation is the transformation of long-lived radioactive isotopes into more stable short-life (< 30 years) isotopes

spallation is used for the treatment of nuclear waste

ELI would be the first infrastructure dedicated to the fundamental study of laser-matter interaction in a new and unsurpassed regime of laser intensity: the ultra-relativistic regime (IL>1023 W/cm²); it would be an exawatt-class laser ~1000 times more powerful than either existing laser; ELI would attain its extreme power from the shortness of its pulses (femtosecond and attosecond)

The infrastructure would serve to investigate a new generation of compact accelerators delivering energetic particles and radiation beams of femtosecond(10-15 s) to attosecond (10-18 s) duration; relativistic compression offers the potential of intensities exceeding IL>1025 W/cm², which would challenge the vacuum critical field as well as provide a new avenue to ultrafast attosecond to zeptosecond (10-21 s) studies of laser-matter interaction.

Romania is one of the 13 members of the consortium formed by European countries and a candidate to host the infrastructure

ELI-PP (Preparatory Phase) is a contract financed by EU FP 7 Program for three years (November 2007 – October 2010) (6 M€)

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ELI will be the first pan-European large-scale facility dedicated to multi-disciplinary applications

ELI would afford wide benefits to society ranging from improvement of oncology treatment, medical imaging, fast electronics and our understanding of aging nuclear reactor materials to development of new methods of nuclear waste processing.

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Principle of CPA – Chirped Pulse Amplification (Mourou 1985)

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The relativistic regime IL > 1018 W/cm2 results in a plethora of novel effects: X-ray generation, γ-ray generation, relativistic self-focusing, high-harmonic generation, electron and proton acceleration, neutron and positron production, as well as the manifestation of nonlinear QED effects

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Relativistic regime: 1 < a0 < 100, a02 = ILλL

2/(1.37 x 1018 Wµm2/cm2)where a0 is the normalized electric field amplitude,IL and λL are the laser intensity and wavelength

At a0 = 1 the electron mass increases by 21/2; the limit a0 ~ 100 corresponds to the 100 TW class lasers

Ultra-relativistic regime: IL > 1023 W/cm2 (a0 ~ 102 – 104)

Extreme Light Infrastructure (ELI) Extreme Light Infrastructure (ELI) projectproject



i.

ii.

iii.


in this novel regime, positrons, pions, muons and neutrinos could be produced as well as high-energy photonsthis largely unexplored intensity territory will provide access to physical effects with much higher characteristic energies and will regroup many subfields of contemporary physics: atomic physics, plasma physics, particle physics, nuclear physics, gravitational physics, nonlinear field theory, ultrahigh-pressure physics, astrophysics and cosmology)the ultra-relativistic regime opens possibilities of:

extreme acceleration of matter so that generation of very energetic particle beams of leptons and hadrons becomes efficient efficient production (~ 10%) of attosecond or even zeptosecond pulses by relativistic compression occurring at rate of 600/a0 [as] study of the field – vacuum interaction effects

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4545High power fs lasers in INFLPR Bucharest

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SErF Fiber Oscillator:- laser radiation at 775 nm- pulse duration 200 fs- repetition rate 35 MHz- energy ~150 pJ (power ~1.5 mW)

Regenerative Amplifier :- laser radiation at 775 nm- pulse duration 200 fs- repetition rate 2 kHz- energy ~700 µJ (power ~1.5 W)

Applications:

Material Processing: micromachining, drilling, laser ablationOptical Spectroscopy: time-resolved fluorescenceCharacterisation: confocal microscopy, fluorescence microscopy

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20052005--20072007 20082008 20092009 20102010 20112011 20122012

4 GW/200 4 GW/200 fsfs(0.7 (0.7 mJmJ))

20 TW/25 20 TW/25 fsfs(400 (400 mJmJ))

10 PW/15 10 PW/15 fsfs(ELI technology)(ELI technology)

LASER CLARK CPA2101LASER CLARK CPA2101


20052005--20072007 20082008 20092009 20102010 20112011 20122012

4 GW/200 4 GW/200 fsfs(0.7 (0.7 mJmJ))

20 TW/25 20 TW/25 fsfs(400 (400 mJmJ))


20 TW LASER (DEC. 2008)20 TW LASER (DEC. 2008)

1 PW/25 1 PW/25 fsfs(25 J)(25 J)

Proton therapyProton therapyXX--ray lasersray lasersOptical coherent Optical coherent tomographytomographyRadiation sourcesRadiation sourcesAccelerated particle sourcesAccelerated particle sources

1 PW/25 1 PW/25 fsfs(25 J)(25 J)


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http://lei2009.inflpr.ro

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20052005--20072007 20082008 20092009 20102010 20112011 20122012

4 GW/200 4 GW/200 fsfs(0.7 (0.7 mJmJ))

20 TW/25 20 TW/25 fsfs(400 (400 mJmJ))


ConclusionsConclusions

* * High intensity and High intensity and ultrashortultrashort pulse laserspulse lasers

* * Exotic physics at high laser intensitiesExotic physics at high laser intensities

* Secondary sources of particles * Secondary sources of particles

* Secondary sources of X* Secondary sources of X--rayray

* * AttosecondAttosecond generationgeneration andand applicationsapplications

* Science and society* Science and society

1 PW/25 1 PW/25 fsfs(25 J)(25 J)


The future of proton therapy requires the construction of specialized centers, equipped with modern diagnostics and medical accelerators near oncological clinics

The construction of small centers would make it possible to provide cheaper facilities for hadrontherapy closer to the patients ⇒ a possible solution is to produce a specialized laser proton accelerator

The use of multi-layer targets with different shapes and composition opens up additional opportunities for controlling the parameters of the fast proton beam, for optimizing its energy spectrum, the number of particles per bunch, the beam focusing and the size of the region where the beam deposits its energy

To increase the duty factor we must use a system of several high-power, 1 Hz repetition rate lasers or to use a multi-stage acceleration scheme in the case of moderate power, high repetition rate (1 kHz) lasers

The generation of fast ions becomes highly effective when the laser radiation reaches the petawatt power limit

By optimizing the laser-target parameters, it becomes possible to accelerate protons up to energies in the several hundred MeV range

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JulyJuly 1155, 2009, 2009 SSummary due dateummary due date

AugustAugust 1155, 2009, 2009 Notification of paper acceptanceNotification of paper acceptance

August August 3131, 200, 20099 Advanced Registration FeeAdvanced Registration Fee

September 15, 2009September 15, 2009 Accommodation deadlineAccommodation deadline

September 15 , 2009September 15 , 2009 Preliminary programPreliminary program

September 15, 2009September 15, 2009 Post deadline papersPost deadline papers

OctoberOctober 1, 20091, 2009 Final program Final program

October 16, 2009 Manuscript due dateOctober 16, 2009 Manuscript due date

October 16October 16--21, 2009 21, 2009 ConferenceConference

Thank you for your attention!Thank you for your attention!

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Documents

Extreme Light Infrastructure (ELI) and Hadron Therapy D. C ... Light Infrastructure... · M. Petrus, A. M. Bratu, S. Banita Department of Lasers, National Institute for Laser, Plasma